|Publication number||US7167747 B2|
|Application number||US 10/436,626|
|Publication date||Jan 23, 2007|
|Filing date||May 13, 2003|
|Priority date||May 13, 2003|
|Also published as||US20040230233, WO2004103172A2, WO2004103172A3|
|Publication number||10436626, 436626, US 7167747 B2, US 7167747B2, US-B2-7167747, US7167747 B2, US7167747B2|
|Inventors||Bruce D. Gunderson, Gillberg M. Jeffrey, Jay M. Wilcox|
|Original Assignee||Medtronic, Inc.|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (19), Referenced by (79), Classifications (13), Legal Events (4)|
|External Links: USPTO, USPTO Assignment, Espacenet|
The present invention generally relates to implantable medical devices, and more particularly relates to reducing effects of oversensing in implantable medical devices.
Implantable medical devices (IMDs) have many functions including the delivery of therapies to cardiac patients, neuro-stimulators, muscular stimulators, and others. Application of the present invention is described below in the context of implantable cardiac pacemakers and/or defibrillators, it being understood that the principles herein may have applicability to other implantable medical devices as well.
An example of an implantable medical device (IMD) includes a device commonly referred to as a pacemaker, which is used to stimulate the heart into a contraction if the sinus node of the heart is not properly timing, or pacing, the contractions of the heart. Modern implantable medical devices also perform many other functions beyond that of pacing. For example, a pacemaker/cardioverter/defibrillator (PCD) performs therapies such as defibrillation and cardioversion as well as providing several different pacing therapies, depending upon the needs of the user and the physiologic condition of the user's heart.
In typical use, a PCD is implanted in a convenient location usually under the skin of the user and in the vicinity of the one or more major arteries or veins. One or more electrical leads connected to the PCD are inserted into or on the heart of the user, usually through a convenient vein or artery. The ends of the leads are placed in contact with the walls or surface of one or more chambers of the heart, depending upon the particular therapies deemed appropriate for the user.
One or more of the leads is adapted to carry a current from the PCD to the heart tissue to stimulate the heart in one of several ways, again depending upon the particular therapy being delivered. The leads are simultaneously used for sensing the physiologic signals provided by the heart to determine when to deliver a therapeutic pulse to the heart, and the nature of the pulse, e.g., a pacing pulse or a defibrillation shock.
In the sensing mode, sense amplifiers coupled to the leads provide amplification to electrogram signals picked up by the sensing electrodes in the heart. The analysis of these signals by the PCD determines whether a therapy (a pacing pulse or a defibrillator shock) should be administered. If erroneous signals are detected by the PCD, an unnecessary therapy may be administered, providing an unnecessary pacing pulse or defibrillator shock to the patient. One cause of erroneous interpretation of sensing signals is oversensing, that is, the false detection of a depolarization event.
Sensing can be accomplished in a number of ways. If two bipolar leads are used, one lead is typically placed within the right ventricle of the heart and a second lead is placed within the right atrium of the heart. Both leads include two sensing elements: a tip electrode that is attached to the wall or surface of the heart, and a ring electrode that is located on the lead but removed some distance from the tip electrode. A high voltage coil located on one or both of the leads can also be used for sensing, as can the implanted PCD can itself. Some cardiac conditions require sensing at both the right ventricle and the right atrium, and still others may add sensing at the left ventricle via a third lead positioned within the coronary sinus. As a result, there are a large number of sensing paths and combinations available for use, depending upon the configuration and programming of the specific implantable device, and some PCDs can be configured to switch to an alternate sensing path if the primary path is determined to be faulty.
Oversensing of cardiac waves may be caused by lead fractures (e.g., conductor break, insulation break, adaptor failure), connectors (e.g. loose set screw), T-wave oversensing, R-wave oversensing, electromagnetic interference (EMI), and myopotentials. In the past, oversensing problems (e.g., myopotentials, T-wave oversensing) have been dealt with by modifying sense amplifiers, filters and PCD lead electrodes. In currently used PCDs the sense amplifiers have self adjusting sensing thresholds for sensitivity, so oversensing often occurs as a result of lead failure. Upon detection of an R-wave, the threshold of the sense amplifier is raised to about 75% of the R-wave. The sense amplifier threshold then decays until the next R-wave is sensed. In this manner the sensing threshold of the sense amplified is continually adjusted to allow for variations in the sensed strength of the R-wave. However, there is still room for improved techniques for eliminating the effects of oversensing.
Accordingly, it is desirable to provide an additional mechanism for dealing with oversensing of depolarization events. In addition, it is desirable to provide an algorithm to be incorporated into detection algorithms in the IMD to prevent the detection and erroneous application of therapies for detected episodes caused by oversensing. Furthermore, other desirable features and characteristics of the present invention will become apparent from the subsequent detailed description and the appended claims, taken in conjunction with the accompanying drawings and the foregoing technical field and background.
A method and apparatus delivering therapy in an implantable medical device that includes sensing a first cardiac signal and detecting cardiac events via a first electrode configuration, determining the presence of an episode requiring therapy in response to the detected cardiac events, sensing a second cardiac signal via a second electrode configuration, comparing, in response to an episode being present, portions of the second cardiac signal corresponding to the detected cardiac events with a predetermined template, and determining whether to deliver therapy in response to the comparing.
The present invention will hereinafter be described in conjunction with the following drawing figures, wherein like numerals denote like elements, and
The following detailed description of the invention is merely exemplary in nature and is not intended to limit the invention or the application and uses of the invention. Furthermore, there is no intention to be bound by any theory presented in the preceding background of the invention or the following detailed description of the invention.
The atrial/SVC lead includes an elongated insulative lead body 15, also carrying three mutually insulated conductors. Located adjacent the J-shaped distal end of the lead are a ring electrode 21 and an extendible helix electrode 17, mounted retractably within an insulative electrode head 19. Each of the electrodes is coupled to one of the conductors within the lead body 15. Electrodes 17 and 21 are employed for atrial pacing and for sensing atrial depolarizations. An elongated coil electrode 23 is provided, proximal to electrode 21 and coupled to the third conductor within the lead body 15. At the proximal end of the lead is a bifurcated connector 13, which carries three electrical connectors, each coupled to one of the coiled conductors.
The coronary sinus lead includes an elongated insulative lead body 6, carrying one conductor, coupled to an elongated coiled defibrillation electrode 8. Electrode 8, illustrated in broken outline, is located within the coronary sinus and great vein of the heart. At the proximal end of the lead is a connector plug 4 that carries an electrical connector, coupled to the coiled conductor.
The pacemaker/cardioverter/defibrillator 10 includes a hermetic enclosure or housing 11 containing the electronic circuitry used for generating cardiac pacing pulses for delivering cardioversion and defibrillation shocks and for monitoring the patient's heart rhythm. Pacemaker/cardioverter/defibrillator 10 is shown with the lead connector assemblies 4, 13 and 14 inserted into the connector block 12, which serves as a receptacle and electrical connector for receiving the connectors 4, 13 and 14 and interconnecting the leads to the circuitry within housing 11. An optional sensor 30 is illustrated schematically by broken outline, and may include one or more of an activity sensor, respiration sensor (potentially from impedance), accelerometer-based posture detector, heart rate detector, ischemia detector and other available physiological sensor known in the art for measuring heart hemodynamics and may be a piezoelectric transducer as known in the art. Sensor 30 may be used, for example, to regulate the underlying pacing rate of the device in rate responsive pacing modes.
Optionally, insulation of the outward facing portion of the housing 11 of the pacemaker/cardioverter/defibrillator 10 may be provided or the outward facing portion may instead be left uninsulated, or some other division between insulated and uninsulated portions may be employed. The uninsulated portion of the housing 11 optionally serves as a subcutaneous defibrillation electrode, used to defibrillate either the atria or ventricles. Other lead configurations and electrode locations may of course be substituted for the lead set illustrated. For example, atrial defibrillation and sensing electrodes might be added to either the coronary sinus lead or the right ventricular lead instead of being located on a separate atrial lead, allowing for a two lead system.
The device is provided with a lead system including electrodes, which may be as illustrated in
Electrodes 310, 311, 318 and 320 are coupled to high voltage output circuit 234. Electrodes 324 and 326 are coupled to the R-wave amplifier 200, which preferably takes the form of an automatic gain controlled amplifier providing an adjustable sensing threshold as a function of the measured R-wave amplitude. A v-sense signal is generated on R-out line 202 whenever the signal sensed between electrodes 324 and 326 exceeds the present sensing threshold.
Electrodes 317 and 321 are coupled to the P-wave amplifier 204, which preferably also takes the form of an automatic gain controlled amplifier providing an adjustable sensing threshold as a function of the measured R-wave amplitude. A signal is generated on P-out line 206 whenever the signal sensed between electrodes 317 and 321 exceeds the present sensing threshold. The general operation of the R-wave and P-wave amplifiers 200 and 204 may correspond to that disclosed in U.S. Pat. No. 5,117,824, by Keimel, et al., issued Jun. 2, 1992, for an Apparatus for Monitoring Electrical Physiologic Signals, incorporated herein by reference in its entirety. However, any of the numerous prior art sense amplifiers employed in implantable cardiac pacemakers, defibrillators and monitors may also usefully be employed in conjunction with the present invention.
Switch matrix 208 is used to select which of the available electrodes are coupled to wide band amplifier 210 for use in digital signal analysis. Selection of electrodes is controlled by the microprocessor 224 via data/address bus 218, which selections may be varied as desired. Signals from the electrodes selected for coupling to bandpass amplifier 210 are provided to multiplexer 220, and thereafter converted to multi-bit digital signals by A/D converter 222, for storage in random access memory 226 under control of direct memory access circuit 228. Microprocessor 224 may employ digital signal analysis techniques to characterize the digitized signals stored in random access memory 226 to recognize and classify the patient's heart rhythm employing any of the numerous signal processing methodologies known to the art.
Telemetry circuit 330 receives downlink telemetry from and sends uplink telemetry to the patient activator by means of antenna 332. Data to be uplinked to the activator and control signals for the telemetry circuit are provided by microprocessor 224 via address/data bus 218. Received telemetry is provided to microprocessor 224 via multiplexer 220. The atrial and ventricular sense amp circuits 200, 204 produce atrial and ventricular EGM signals which also may be digitized and uplink telemetered to an associated programmer on receipt of a suitable interrogation command. The device may also be capable of generating so-called marker codes indicative of different cardiac events that it detects. A pacemaker with marker-channel capability is described, for example, in U.S. Pat. No. 4,374,382 to Markowitz, incorporated by reference herein in its entirety. The particular telemetry system employed is not critical to practicing the invention, and any of the numerous types of telemetry systems known for use in implantable devices may be used. In particular, the telemetry systems as disclosed in U.S. Pat. No. 5,292,343 issued to Blanchette et al., U.S. Pat. No. 5,314,450, issued to Thompson, U.S. Pat. No. 5,354,319, issued to Wyborny et al. U.S. Pat. No. 5,383,909, issued to Keimel, U.S. Pat. No. 5,168,871, issued to Grevious, U.S. Pat. No. 5,107,833 issued to Barsness or U.S. Pat. No. 5,324,315, issued to Grevious, all incorporated herein by reference in their entireties, are suitable for use in conjunction with the present invention. However, the telemetry systems disclosed in the various other patents cited herein which are directed to programmable implanted devices, or similar systems may also be substituted. The telemetry circuit 330 is of course also employed for communication to and from an external programmer, as is conventional in implantable anti-arrhythmia devices.
The device of
The remainder of the circuitry is dedicated to the provision of cardiac pacing, cardioversion and defibrillation therapies, and, for purposes of the present invention may correspond to circuitry known in the prior art. An exemplary apparatus is disclosed for accomplishing pacing, cardioversion and defibrillation functions as follows. The pacer timing/control circuitry 212 includes programmable digital counters which control the basic time intervals associated with DDD, VVI, DVI, VDD, AAI, DDI, DDDR, VVIR, DVIR, VDDR, AAIR, DDIR and other modes of single and dual chamber pacing well known to the art. Circuitry 212 also controls escape intervals associated with anti-tachyarrhythmia pacing in both the atrium and the ventricle, employing, any anti-tachyarrhythmia pacing therapies known to the art.
Intervals defined by pacing circuitry 212 include atrial and ventricular pacing escape intervals, the refractory periods during which sensed P-waves and R-waves are ineffective to restart timing of the escape intervals and the pulse widths of the pacing pulses. The durations of these intervals are determined by microprocessor 224, in response to stored data in memory 226 and are communicated to the pacing circuitry 212 via address/data bus 218. Pacer circuitry 212 also determines the amplitude of the cardiac pacing pulses under control of microprocessor 224.
During pacing, the escape interval counters within pacer timing/control circuitry 212 are reset upon sensing of R-waves and P-waves as indicated by signals on lines 202 and 206, and in accordance with the selected mode of pacing on time-out trigger generation of pacing pulses by pacer output circuits 214 and 216, which are coupled to electrodes 317, 321, 324 and 326. The escape interval counters are also reset on generation of pacing pulses, and thereby control the basic timing of cardiac pacing functions, including anti-tachyarrhythmia pacing.
The durations of the intervals defined by the escape interval timers are determined by microprocessor 224, via data/address bus 218. The value of the count present in the escape interval counters when reset by sensed R-waves and P-waves may be used to measure the durations of R-R intervals, P-P intervals, PR intervals and R-P intervals, which measurements are stored in memory 226 and are used in conjunction with the present invention to determine oversensing and in conjunction with tachyarrhythmia detection functions.
Microprocessor 224 operates as an interrupt driven device, and is responsive to interrupts from pacer timing/control circuitry 212 corresponding to the occurrences of sensed P-waves and R-waves and corresponding to the generation of cardiac pacing pulses. These interrupts are provided via data/address bus 218. Any necessary mathematical calculations to be performed by microprocessor 224 and any updating of the values or intervals controlled by pacer timing/control circuitry 212 take place following such interrupts. Microprocessor 224 includes associated ROM in which the stored program controlling its operation as described below resides. A portion of the memory 226 may be configured as a plurality of recirculating buffers, capable of holding series of measured intervals, which may be analyzed in response to the occurrence of a pace or sense interrupt to determine whether the patient's heart is presently exhibiting atrial or ventricular tachyarrhythmia.
The arrhythmia detection method of the present invention may include any of the numerous available prior art tachyarrhythmia detection algorithms. One preferred embodiment may employ all or a subset of the rule-based detection methods described in U.S. Pat. No. 5,545,186 issued to Olson et al. or in U.S. Pat. No. 5,755,736 issued to Gillberg et al., both incorporated herein by reference in their entireties. However, any of the various arrhythmia detection methodologies known to the art might also usefully be employed in alternative embodiments of the invention.
In the event that an atrial or ventricular tachyarrhythmia is detected, and an anti-tachyarrhythmia pacing regimen is desired, timing intervals for controlling generation of anti-tachyarrhythmia pacing therapies are loaded from microprocessor 224 into the pacer timing and control circuitry 212, to control the operation of the escape interval counters therein and to define refractory periods during which detection of R-waves and P-waves is ineffective to restart the escape interval counters.
In the event that generation of a cardioversion or defibrillation pulse is required, microprocessor 224 employs the escape interval counter to control timing of such cardioversion and defibrillation pulses, as well as associated refractory periods. In response to the detection of atrial or ventricular fibrillation or tachyarrhythmia requiring a cardioversion pulse, microprocessor 224 activates cardioversion/defibrillation control circuitry 230, which initiates charging of the high voltage capacitors 246, 248 via charging circuit 236, under control of high voltage charging control line 240. The voltage on the high voltage capacitors is monitored via VCAP line 244, which is passed through multiplexer 220 and in response to reaching a predetermined value set by microprocessor 224, results in generation of a logic signal on Cap Full (CF) line 254, terminating charging. Thereafter, timing of the delivery of the defibrillation or cardioversion pulse is controlled by pacer timing/control circuitry 212. Following delivery of the fibrillation or tachycardia therapy the microprocessor then returns the device to cardiac pacing and awaits the next successive interrupt due to pacing or the occurrence of a sensed atrial or ventricular depolarization. In the illustrated device, delivery of the cardioversion or defibrillation pulses is accomplished by output circuit 234, under control of control circuitry 230 via control bus 238. Output circuit 234 determines whether a monophasic or biphasic pulse is delivered, whether the housing 311 serves as cathode or anode and which electrodes are involved in delivery of the pulse.
An examination of far-field signal 42, however, shows a relatively regular far-field R-wave. During the period of relative normal R-wave representation 44, the far-field signal 42 follows the near-field signal 40 quite closely. When the near-field signal 40 becomes erratic in an erratic portion 46, the far-field signal 42 continues to show regular R-wave far-field pulses indicating that the erratic portion 46 may be due to oversensing. As the near-field signal 40 recovers at a period of relative normal R-wave representation 48, the far-field signal 42 continues to follow the near-field signal 40, suggesting that the irregular portion 46 of the near-field signal 40 was due to oversensing, and probably an intermittent failure, since the R-wave pulses of near-field signal 40 recovered at period of relative normal R-wave representation 48.
With a pattern of this nature, it would be premature to deliver a therapy to the patient, particularly a painful defibrillation shock. Typically several methods are used to avoid delivering a shock under these conditions. First, if there is a detection of an irregularity as seen in the erratic portion 46 of near-field signal 40, one can wait to see whether the problem goes away by increasing the number of intervals for detection (as is the case in the waves of
The decision to administer a therapy has been based primarily upon the near-field R-wave. The present invention uses the far-field electrogram to discriminate QRS complexes between supraventricular (e.g. sinus tachycardia, atrial fibrillation) and ventricular arrhythmias. In this way, the present invention provides an algorithm that takes into account other information to provide a better determination of an actual arrhythmia before subjecting a patient to a painful defibrillation shock. The algorithm uses far-field QRS complexes converted to wavelet coefficients to identify both sinus R-waves and noise components (based on an isoelectric baseline for a far-field electrogram) during oversensing. As each ventricular event is sensed on the near-field electrogram, the QRS complex is checked against a stored template to determine whether there was a sinus beat using a match percentage. The sensed R-waves would have a high percentage match with the sinus template and the sensed noise would have a low percentage match. The far-field electrogram isoelectric baseline is determined by calculating the sum of successive samples in the electrogram window. The use of additional information in analyzing R-wave patterns can be useful in identifying an oversensing condition, which, if present, allows the administration of a therapy shock to be delayed until oversensing is confirmed.
If the percentage match of two to four events of the eight ordered events M1–M8 is not 70% or greater, oversensing is not detected, and therefore therapy is delivered in the normal fashion described above, i.e., therapy is not inhibited because of determined oversensing, Step 78. On the other hand, if the percentage match of two to four events of the eight ordered events M1–M8 are 70% or greater, a determination is made as to whether the difference between the template match percentages of the seventh ordered R-wave M7 and the third ordered R-wave M3, i.e., the interquartile percentage range M7−M3, is greater than a selected threshold, Step 72, such as 30%, for example. Again this threshold is somewhat arbitrary and may be subject to modification as set forth above with respect to the determination at Step 70.
If the interquartile range is not greater than the selected threshold, oversensing is not detected, and therefore therapy is delivered in the normal fashion described above, i.e., therapy is not inhibited because of determined oversensing, Step 78. On the other hand, if the interquartile range is greater than the selected threshold, a determination is made as to whether an interquartile variability, i.e., the difference between the match percentages of the seventh ordered R-wave M7 and the third ordered R-wave M3 (M7−M3) divided by the sum of the seventh ordered R-wave M7 and the third ordered R-wave M3 (M7+M3), is greater than a predetermined threshold, Step 74, such as 20%, for example. As with the other thresholds, this threshold is subject to modification in a particular device for the same reasons given above. If the interquartile variability is not greater than the predetermined threshold, oversensing is not detected, and therefore therapy is delivered in the normal fashion described above, i.e., therapy is not inhibited because of determined oversensing, Step 78. On the other hand, if interquartile variability is greater than the predetermined threshold, oversensing is detected, and therapy is withheld, Step 76. The two determinations of Steps 72 and 74 taken together, if successfully passed, offer evidence of a bimodal distribution of matches. If there is in fact a bimodal distribution this is evidence of oversensing, since some true sinus R-waves were detected at Step 70, and there are, by virtue of the determinations at Steps 72 and 74, some non-sinus R-waves.
As an example of the operation of the method illustrated in
Clearly the percentage match of two to four of the eight ordered sensed events is met, Step 70, since two of the percentages, M7 and M8, are above 70%. The interquartile range criterion is also met, Step 72, since the difference between the seventh ordered R-wave and the third ordered R-wave, M7−M3 (85−28=57) is greater than 30%, and the interquartile variability criterion is met, Step 74, since the difference between the match percentages of the seventh ordered R-wave and the third ordered R-wave divided by the sum of the seventh ordered R-wave and the third ordered R-wave (M7−M3)/(M7+M3) (57/113=50.4%) is greater than 20%. Thus in this instance therapy would be withheld because of strong evidence of oversensing.
Likewise, consider the following values for corresponding to the percentage match of the eight most recently sensed events with the template wave:
With this set of percentages obviously none of the criteria of Steps 70, 72 and 74 are met, and therefore oversensing would not be detected and therefore therapy would not be withheld.
Once a VF episode is verified, R-R intervals corresponding to the previous M sensed events are evaluated (The numbers under the marker channel 23 in
If none of the evaluated R-R intervals is less than the predetermined threshold, the VF detection process for delivering a corresponding shock therapy continues according to the normal VF detection process, Step 108. However, if there is a possibility of oversensing, i.e., the sensed events include one or more R-R intervals that are less than the predetermined threshold rate, a determination is made as to whether a far-field signal sensed between secondary electrodes within a window of time corresponding to the last eight sensed events matches a predetermined waveform template corresponding to sensing of a sinus beat within a predetermined match threshold, Step 88. As described above, the secondary electrodes for sensing the far-field signal include the lead coil 20 and the uninsulated portion of the housing 11, for example, or a sensing lead 6, 15 in another part of the heart alone or in combination with the uninsulated portion of the housing 11.
In particular, referring back to
If none of the waveforms of the far-field sensed events are determined to correspond to a sinus beat, i.e., none of the last eight sensed far-field events matches the predetermined waveform template within the predetermined match threshold, the VF detection process for delivering a corresponding shock therapy continues according to the normal VF detection process, Step 108. However, if it is determined that one or more of the last eight sensed far-field events matches the waveform template within the match threshold, a determination is made as to whether the corresponding far-field signal sensed between the secondary electrodes is below a predetermined baseline threshold indicative of an isoelectric baseline, Step 90. In particular, a determination is made as to whether the summation of the portion of the far-field signal within each window 204 corresponding to the previous eight sensed events 202 is less than a predetermined baseline threshold, such as 3 ms. It is understood that any value may be chosen for the baseline threshold, and therefore the present invention is not intended to be limited to the use of a 3 ms baseline threshold. In this way, identification of an isoelectric baseline in the far-field signal is utilized a third factor in verifying that oversensing is taking place. In addition, methods other than summing the EGM samples may also be utilized to determine a stable far-field signal. For example, a sum of successive differences between events could be used to indicate no change when the sum of successive differences is determined to be less than a predetermined difference threshold.
If it is determined that the far-field signal within the window about each of the sensed events 206 is not below the baseline threshold, the VF detection process for delivering a corresponding shock therapy continues according to the normal VF detection process, Step 108. On the other hand, if the far-field signal within the window about one or more of the previous sensed events is determined to be less than the baseline threshold, a patient alert is activated to alert the patient to have the implanted device checked by their physician. The patient alert may include an audio tone, vibration or other alert. Since at this point all three tests at Steps 86, 88, and 90 have been affirmative, the detected VF episode was most likely caused by oversensing, and therefore the capacitor charging and therapy to the patient is delayed and the IMD goes into a redetect mode to verify the existence of oversensing, Step 94.
During the redetect mode, Step 94, a determination is made as to whether the detected episode has self terminated, Step 98, by evaluating R-R intervals corresponding to sensed V-events occurring subsequent to the detected episode, Step 96, and determining whether a predetermined number of sinus beats, such as eight consecutive sinus beats, for example, are sensed subsequent to the detected episode. Again, self-termination may be determined in response to any number of sensed sinus beats, and therefore it is understood that the present invention is not intended to be limited to the use of eight sinus beats to indicate self-termination of the VF episode. If the detected episode has terminated, Yes in Step 98, the counters are reset and the process waits for the next detected episode, Step 80. If the detected episode has not terminated, a determination is made as to whether a predetermined number of VF events, i.e., a redetection number of intervals for detection (RNID) of ventricular fibrillation (VF), have occurred in order to verify the detected episode, Step 100. For example, a VF episode is determined to be taking place during redetection when it is determined that N out of the last M subsequently sensed events correspond to VF events, such as 6 out 8 subsequently sensed events correspond to VF events. However, it is understood that, according to the present invention, any desired values may be utilized for the RNID.
If the predetermined number of VF events have not occurred, No in Step 100, the process is repeated upon receipt of the next subsequent sensed event, Step 96. Once the detected episode is verified in Step 100, i.e., 6 out of 8 subsequently sensed events correspond to a VF event, a determination is made as to whether a redetection timer has expired, Step 102. If the redetection timer has expired and the redetection of oversensing has not been confirmed, the VF detection process for delivering a corresponding shock therapy continues according to the normal VF detection process, Step 108. If the redetection timer has not expired, a determination is made as to whether oversensing is confirmed by the subsequently sensed events 210 (
If oversensing is not confirmed, the VF detection process for delivering a corresponding shock therapy continues according to the normal VF detection process, Step 108. If oversensing is confirmed, the redetect counters are reset, Step 106, and the process is repeated with the next sensed event, Step 96. In this way, the present invention continues to withhold the delivery of therapy because of oversensing unless the oversensing cannot be confirmed, NO in Step 104, the detected episode terminates itself, YES in Step 98, or the timer has expired before the detected episode self terminates or the oversensing fails to be confirmed, Step 102. The redetect timer is a timer that may be set by a doctor depending on the condition of the patient, and represents the time the doctor is willing to allow to delay therapy for a true ventricular arrhythmia. According to an embodiment of the present invention, the timer is set at 5 seconds, although it is understood that any value can be chosen as desired.
If two oversensing criteria have not been met, a the far-field signal sensed between the secondary electrodes corresponding to the subsequent sensed events 210 is compared to the baseline threshold indicative of an isoelectric baseline in the corresponding EGM, Step 190. A determination is then made, Step 191, as to whether two oversensing criteria have been met, i.e., both one or more of the R-R intervals are less than the threshold rate and the far-field signal sensed between the secondary electrodes corresponding to the subsequent sensed events 210 is less than the baseline threshold, similar to satisfying both Steps 86 and 90 in
In this way, in the method of detecting oversensing illustrated in
Other embodiments, based on variations in the embodiments describe in
It should be noted that upon the occurrence of a therapy shock being administered, a number of the R-waves (both near-field and far-field) both prior to and subsequent to the shock are stored within the ICD for later read-out and analysis by a doctor. Depending upon the amount of storage memory within the ICD, the duration of stored waves prior to and after the therapy, and the number of waves stored (i.e. near-field, far-field, others) a number of events can be stored over a period of days or longer. If, for example there is stored only the near-field R-wave, twenty or more minutes of storage would allow forty separate events to be stored. If near-field and far-field R-waves were stored, perhaps only ten minutes would be available for storage. Because of the ability to store several traces of R-waves or other waves of an electrogram, the read-out could also be used in a remote monitoring system in which a patient may connect, for example, a home monitor that downloads the information for later transmission by modem or other convenient means to a doctor's office.
While at least one exemplary embodiment has been presented in the foregoing detailed description, it should be appreciated that a vast number of variations exist. It should also be appreciated that the exemplary embodiment or exemplary embodiments are only examples, and are not intended to limit the scope, applicability, or configuration of the invention in any way. Rather, the foregoing detailed description will provide those skilled in the art with a convenient road map for implementing the exemplary embodiment or exemplary embodiments. It should be understood that various changes can be made in the function and arrangement of elements without departing from the scope of the invention as set forth in the appended claims and the legal equivalents thereof.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US4374382||Jan 16, 1981||Feb 15, 1983||Medtronic, Inc.||Marker channel telemetry system for a medical device|
|US4428378||Nov 19, 1981||Jan 31, 1984||Medtronic, Inc.||Rate adaptive pacer|
|US5107833||Nov 2, 1990||Apr 28, 1992||Medtronic, Inc.||Telemetry gain adjustment algorithm and signal strength indication in a noisy environment|
|US5117824||Nov 14, 1990||Jun 2, 1992||Medtronic, Inc.||Apparatus for monitoring electrical physiologic signals|
|US5168871||Nov 9, 1990||Dec 8, 1992||Medtronic, Inc.||Method and apparatus for processing quasi-transient telemetry signals in noisy environments|
|US5193550 *||Nov 30, 1990||Mar 16, 1993||Medtronic, Inc.||Method and apparatus for discriminating among normal and pathological tachyarrhythmias|
|US5292343||Jun 10, 1992||Mar 8, 1994||Medtronic, Inc.||Hand shake for implanted medical device telemetry|
|US5324315||Aug 12, 1993||Jun 28, 1994||Medtronic, Inc.||Closed-loop downlink telemetry and method for implantable medical device|
|US5354319||Jan 29, 1993||Oct 11, 1994||Medtronic, Inc.||Telemetry system for an implantable medical device|
|US5383909||Jan 29, 1993||Jan 24, 1995||Medtronic, Inc.||Diagnostic telemetry system for an apparatus for detection and treatment of tachycardia and fibrillation|
|US5447519 *||Mar 19, 1994||Sep 5, 1995||Medtronic, Inc.||Method and apparatus for discrimination of monomorphic and polymorphic arrhythmias and for treatment thereof|
|US5545186||Mar 30, 1995||Aug 13, 1996||Medtronic, Inc.||Prioritized rule based method and apparatus for diagnosis and treatment of arrhythmias|
|US5558098 *||Nov 2, 1995||Sep 24, 1996||Ventritex, Inc.||Method and apparatus for detecting lead sensing artifacts in cardiac electrograms|
|US5620466||Aug 14, 1995||Apr 15, 1997||Cardiac Pacemakers, Inc.||Digital AGC using separate gain control and threshold templating|
|US5755736||Jul 16, 1997||May 26, 1998||Medtronic, Inc.||Prioritized rule based method and apparatus for diagnosis and treatment of arrhythmias|
|US5755739||Dec 4, 1996||May 26, 1998||Medtronic, Inc.||Adaptive and morphological system for discriminating P-waves and R-waves inside the human body|
|US5776168||Apr 3, 1996||Jul 7, 1998||Medtronic, Inc.||EGM recording system for implantable medical device|
|US6266554 *||Feb 12, 1999||Jul 24, 2001||Cardiac Pacemakers, Inc.||System and method for classifying cardiac complexes|
|US6393316||May 8, 2000||May 21, 2002||Medtronic, Inc.||Method and apparatus for detection and treatment of cardiac arrhythmias|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US7266409 *||Apr 15, 2005||Sep 4, 2007||Medtronic, Inc.||Method and apparatus for determining oversensing in a medical device|
|US7774063 *||Aug 10, 2010||Medtronic, Inc.||Method and apparatus for discriminating cardiac signals in a medical device based on wavelet decomposition analysis|
|US7783340||Jan 16, 2007||Aug 24, 2010||Cameron Health, Inc.||Systems and methods for sensing vector selection in an implantable medical device using a polynomial approach|
|US7894886 *||May 4, 2007||Feb 22, 2011||Medtronic, Inc.||Method and apparatus for discriminating cardiac signals in a medical device based on wavelet decomposition analysis|
|US7953488||May 31, 2011||Medtronic, Inc.||Pre-qualification of an alternate sensing configuration|
|US7974690||Jul 5, 2011||Medtronic, Inc.||Lead integrity testing during suspected tachyarrhythmias|
|US8050750 *||Jan 27, 2009||Nov 1, 2011||Medtronic, Inc.||Event discrimination using unipolar and bipolar signal differences|
|US8078277||Oct 29, 2008||Dec 13, 2011||Medtronic, Inc.||Identification and remediation of oversensed cardiac events using far-field electrograms|
|US8126553||Jul 25, 2008||Feb 28, 2012||Medtronic, Inc.||Sensing integrity determination based on cardiovascular pressure|
|US8160686||Apr 17, 2012||Cameron Health, Inc.||Methods and devices for accurately classifying cardiac activity|
|US8160687||Apr 17, 2012||Cameron Health, Inc.||Methods and devices for accurately classifying cardiac activity|
|US8200322||Jun 12, 2012||Medtronic, Inc.||Electrogram storage for suspected non-physiological episodes|
|US8200341||Feb 7, 2007||Jun 12, 2012||Cameron Health, Inc.||Sensing vector selection in a cardiac stimulus device with postural assessment|
|US8260419||Oct 27, 2009||Sep 4, 2012||Medtronic, Inc.||Non-sustained tachyarrhythmia analysis to identify lead related condition|
|US8265737 *||Sep 11, 2012||Cameron Health, Inc.||Methods and devices for identifying overdetection of cardiac signals|
|US8265749||Dec 14, 2009||Sep 11, 2012||Cameron Health, Inc.||Methods and devices for accurately classifying cardiac activity|
|US8280507||Jun 10, 2009||Oct 2, 2012||Biotronik Crm Patent Ag||Cardiac stimulator for treatment of tachycardiac arrhythmias of the heart|
|US8396543||Jan 28, 2010||Mar 12, 2013||Medtronic, Inc.||Storage of data for evaluation of lead integrity|
|US8428697||Jan 22, 2009||Apr 23, 2013||Medtronic, Inc.||“Blurred template” approach for arrhythmia detection|
|US8437840||May 7, 2013||Medtronic, Inc.||Episode classifier algorithm|
|US8494630||Jan 16, 2009||Jul 23, 2013||Cameron Health, Inc.||Data manipulation following delivery of a cardiac stimulus in an implantable cardiac stimulus device|
|US8521281||Oct 14, 2011||Aug 27, 2013||Medtronic, Inc.||Electrogram classification algorithm|
|US8532772||Nov 28, 2006||Sep 10, 2013||Medtronic, Inc.||Method and apparatus for post-processing of episodes detected by a medical device|
|US8548573||Jan 18, 2010||Oct 1, 2013||Cameron Health, Inc.||Dynamically filtered beat detection in an implantable cardiac device|
|US8565878||Mar 6, 2009||Oct 22, 2013||Cameron Health, Inc.||Accurate cardiac event detection in an implantable cardiac stimulus device|
|US8588896||Sep 7, 2012||Nov 19, 2013||Cameron Health, Inc.||Methods and devices for accurately classifying cardiac activity|
|US8600489||Mar 30, 2012||Dec 3, 2013||Cameron Health, Inc.||Methods and devices for accurately classifying cardiac activity|
|US8626280||Mar 30, 2012||Jan 7, 2014||Cameron Health, Inc.||Methods and devices for accurately classifying cardiac activity|
|US8644931||Jul 25, 2008||Feb 4, 2014||Medtronic, Inc.||Impedance variability analysis to identify lead-related conditions|
|US8660643||Aug 8, 2012||Feb 25, 2014||Medtronic, Inc.||Non-sustained tachyarrhythmia analysis to identify lead related condition|
|US8694097||Jun 30, 2010||Apr 8, 2014||Medtronic, Inc.||Multi-channel sensing methods in implantable cardiovertor defibrillators|
|US8700152||May 21, 2013||Apr 15, 2014||Cameron Health, Inc.||Data manipulation following delivery of a cardiac stimulus in an implantable cardiac stimulus device|
|US8712523||Dec 11, 2009||Apr 29, 2014||Cameron Health Inc.||Implantable defibrillator systems and methods with mitigations for saturation avoidance and accommodation|
|US8744555||Oct 27, 2010||Jun 3, 2014||Cameron Health, Inc.||Adaptive waveform appraisal in an implantable cardiac system|
|US8744560||Sep 30, 2011||Jun 3, 2014||Medtronic, Inc.||Electrogram summary|
|US8768459||Jul 30, 2012||Jul 1, 2014||Medtronic, Inc.||Morphology-based precursor to template matching comparison|
|US8774909||Sep 26, 2011||Jul 8, 2014||Medtronic, Inc.||Episode classifier algorithm|
|US8781585||Nov 21, 2011||Jul 15, 2014||Medtronic, Inc.||Identification and remediation of oversensed cardiac events using far-field electrograms|
|US8781602||Jun 17, 2013||Jul 15, 2014||Cameron Health, Inc.||Sensing vector selection in a cardiac stimulus device with postural assessment|
|US8788023||May 26, 2006||Jul 22, 2014||Cameron Health, Inc.||Systems and methods for sensing vector selection in an implantable medical device|
|US8880161||Oct 21, 2013||Nov 4, 2014||Cameron Health, Inc.||Methods and devices for accurately classifying cardiac activity|
|US8886296||Oct 14, 2011||Nov 11, 2014||Medtronic, Inc.||T-wave oversensing|
|US8929977||Dec 4, 2013||Jan 6, 2015||Cameron Health, Inc.||Methods and devices for accurately classifying cardiac activity|
|US8965491||Apr 7, 2014||Feb 24, 2015||Cameron Health, Inc.||Adaptive waveform appraisal in an implantable cardiac system|
|US8965530||Jun 18, 2014||Feb 24, 2015||Cameron Health, Inc.||Implantable cardiac devices and methods using an x/y counter|
|US9037240||Jul 25, 2008||May 19, 2015||Medtronic, Inc.||Electrode lead integrity reports|
|US9079035||Jun 6, 2013||Jul 14, 2015||Cameron Health, Inc.||Electrode spacing in a subcutaneous implantable cardiac stimulus device|
|US9149637||Jun 29, 2010||Oct 6, 2015||Cameron Health, Inc.||Adaptive confirmation of treatable arrhythmia in implantable cardiac stimulus devices|
|US9149645||Mar 10, 2014||Oct 6, 2015||Cameron Health, Inc.||Methods and devices implementing dual criteria for arrhythmia detection|
|US9162074||Nov 24, 2014||Oct 20, 2015||Cameron Health, Inc.||Methods and devices for accurately classifying cardiac activity|
|US9242112||Feb 20, 2014||Jan 26, 2016||Cameron Health, Inc.||Data manipulation following delivery of a cardiac stimulus in an implantable cardiac stimulus device|
|US9265432||May 23, 2014||Feb 23, 2016||Cameron Health, Inc.||Methods and devices for accurately classifying cardiac activity|
|US9339662||Oct 18, 2013||May 17, 2016||Cameron Health, Inc.||Methods and devices for accurately classifying cardiac activity|
|US9357969||Jul 29, 2015||Jun 7, 2016||Cameron Health, Inc.||Sensing vector selection in a cardiac stimulus device with postural assessment|
|US9364677||Jun 13, 2014||Jun 14, 2016||Cameron Health, Inc.||Systems and methods for sensing vector selection in an implantable medical device|
|US9421390||Sep 11, 2015||Aug 23, 2016||Cameron Health Inc.||Methods and devices implementing dual criteria for arrhythmia detection|
|US20050049644 *||Jul 27, 2004||Mar 3, 2005||Cameron Health, Inc.||Multiple electrode vectors for implantable cardiac treatment devices|
|US20060116730 *||Apr 15, 2005||Jun 1, 2006||Gunderson Bruce D||Method and apparatus for determining oversensing in a medical device|
|US20070123941 *||Nov 28, 2006||May 31, 2007||Gunderson Bruce D||Method and apparatus for post-processing of episodes detected by a medical device|
|US20070260152 *||May 4, 2007||Nov 8, 2007||Ghanem Raja N||Method and apparatus for discriminating cardiac signals in a medical device based on wavelet decomposition analysis|
|US20070260153 *||May 4, 2007||Nov 8, 2007||Ghanem Raja N|
|US20070276447 *||May 26, 2006||Nov 29, 2007||Cameron Health, Inc.||Implantable medical devices and programmers adapted for sensing vector selection|
|US20080172098 *||Jan 3, 2008||Jul 17, 2008||Gunderson Bruce D||Method and apparatus for reducing inappropriate detection of lead-related noise|
|US20090299201 *||Dec 3, 2009||Medtronic, Inc.||Electrode lead integrity reports|
|US20090299421 *||Jul 24, 2008||Dec 3, 2009||Medtronic, Inc.||Evaluation of implantable medical device sensing integrity based on evoked signals|
|US20090299429 *||Jul 25, 2008||Dec 3, 2009||Medtronic, Inc.||Sensing integrity determination based on cardiovascular pressure|
|US20090299432 *||Jul 25, 2008||Dec 3, 2009||Metronic, Inc.||Impedance variability analysis to identify lead-related conditions|
|US20090312812 *||Jun 10, 2009||Dec 17, 2009||Thomas Doerr||Cardiac stimulator for treatment of tachycardiac arrhythmias of the heart|
|US20090326600 *||Dec 31, 2009||Medtronic, Inc.||Lead integrity testing during suspected tachyarrhythmias|
|US20100023084 *||Jan 28, 2010||Medtronic, Inc.||Lead integrity testing triggered by sensed signal saturation|
|US20100030289 *||Feb 4, 2010||Medtronic, Inc.||Pre-qualification of an alternate sensing configuration|
|US20100094369 *||Dec 14, 2009||Apr 15, 2010||Cameron Health, Inc.||Methods and Devices for Accurately Classifying Cardiac Activity|
|US20100106209 *||Oct 29, 2008||Apr 29, 2010||Medtronic, Inc.||Identification and remediation of oversensed cardiac events using far-field electrograms|
|US20100185109 *||Jul 22, 2010||Medtronic, Inc.||"blurred template" approach for arrhythmia detection|
|US20100191132 *||Jan 27, 2009||Jul 29, 2010||Medtronic, Inc.||Event Discrimination Using Unipolar and Bipolar Signal Differences|
|US20110098585 *||Apr 28, 2011||Cameron Health, Inc.||Methods and Devices for Identifying Overdetection of Cardiac Signals|
|US20110098766 *||Oct 27, 2009||Apr 28, 2011||Medtronic, Inc.||Non-sustained tachyarrhythmia analysis to identify lead related condition|
|US20110098775 *||Apr 28, 2011||Cameron Health, Inc.||Adaptive Waveform Appraisal in an Implantable Cardiac System|
|US20110184481 *||Jan 28, 2010||Jul 28, 2011||Medtronic, Inc.||Storage of data for evaluation of lead integrity|
|U.S. Classification||607/9, 600/518, 607/27, 600/515, 607/5|
|International Classification||A61N1/362, A61N1/39, A61N1/372, A61N1/37|
|Cooperative Classification||A61N1/3622, A61N1/3704|
|European Classification||A61N1/362A2, A61N1/37B2|
|Sep 5, 2003||AS||Assignment|
Owner name: MEDTRONIC, INC., MINNESOTA
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:GUNDERSON, BRUCE D.;GILLBERG, JEFFREY M.;WILCOX, JAY M.;REEL/FRAME:014454/0992;SIGNING DATES FROM 20030513 TO 20030819
|Jun 22, 2010||FPAY||Fee payment|
Year of fee payment: 4
|Jul 20, 2010||CC||Certificate of correction|
|Jul 23, 2014||FPAY||Fee payment|
Year of fee payment: 8